Laser-assisted thermal separation of tissue

ABSTRACT

A laser-assisted method for fully or partially separating tissue such as collagen-containing tissue is provided. In one embodiment, the method pertains to a capsolurorhexis whereby the laser-assisted method is applied to the lens capsule. A light-absorbing agent is added into or onto the tissue. A light beam with a wavelength capable of being absorbed by the light absorbing agent is then directed at the tissue to cause a thermal effect at the tissue following a predetermined closed curve with the goal to avoid irregularity or potential tears in the resulting rim of the tissue.

CROSS-REFERENCE TO RELATED APPLICATIONS

This application is a continuation of U.S. patent application Ser. No. 12/286,020 filed Sep. 26, 2008, now U.S. Pat. No. 8,409,182 issued on Apr. 2, 2013, which is incorporated herein by reference. U.S. patent application Ser. No. 12/286,020 filed Sep. 26, 2008 claims priority from U.S. Provisional Application Nos. 60/995,792, filed on Sep. 28, 2007, which is incorporated herein by reference.

FIELD OF THE INVENTION

The present invention relates to surgeries and procedures for removing or separating tissue. In particular, the invention relates methods and devices for performing a capsulorhexis.

BACKGROUND OF THE INVENTION

Cataracts are a common cause for poor vision. They are the leading cause of blindness with a prevalence of over 20M worldwide. In addition, there are at least 100M eyes with cataracts causing visual acuity of less that 6/60 in meters (or 20/200 in feet). Cataract extraction is the most commonly performed surgical procedures in the world with estimates of 10 million cases worldwide and 2 million cases being performed annually in North America. There are three types of cataract extraction: intracapsular, small incision cataract and phacoemulsification.

Currently, intracapsular surgery is commonly performed in the developing countries where there are less resources. In this procedure both the opacified natural lens and the lens capsule are removed together.

In small incision cataract surgery and phacoemulsification the opacified natural lens is removed while leaving the elastic lens capsule intact to allow implantation and retention of the intraocular lens (IOL). One of the more critical surgical component is the capsulorhexis.

Capsulorhexis is the incision in the lens capsule to permit removal of the lens nucleus and cortex. The lens capsule is a transparent, homogeneous basement membrane that is made up of collagen-like protein. It has elastic properties without being composed of elastic fibers. The capsule has a smooth surface contour except at its equator where the zonules attach.

Ideally the capsulorhexis creates a symmetric circular incision, centered about the optical axis and is sized appropriately for the IOL and patient's condition. The mechanical integrity around the newly formed incision edge needs to be sufficient to withstand the forces experienced during cataract extraction and IOL implantation. By maintaining integrity of the remaining capsule, the IOL haptics are located in proximity of the capsule equator to allow location of the IOL. Postoperatively the newly formed capsule rim hardens and the opening contracts providing further strengthen and structural support for the IOL to prevent dislocation and misalignment. Because of this postoperative contraction it is important that the opening diameter and the IOL optic diameter are purposefully mismatched, otherwise the resultant pressures may cause the IOL to be dislocate.

The current standard of care for capsulorhexis is Continuous Curvilinear Capsulorhexis (CCC). The concept of the CCC is to provide a smooth continuous circular opening through the anterior lens capsule for phacoemulsification and insertion of the intraocular lens minimizing the risk of complications including errant tears and extensions. Currently, the capsulorhexis is performed manually utilizing forceps or a needle. The technique is dependent on applying a shear force and minimizing in-plane stretching forces to manually tear the incision.

The size of the capsulorhexis is determined by technique, the zonules strength and IOL optic diameter. Zonular strength is assessed prior to capsulorhexis. If the zonules appear strong then the capsulorhexis diameter should measure about 4-5 mm being about 0.5 to 1.0 mm smaller than the IOL optic diameter and centered on the optical axis. This provides overlap with the IOL and some margin for error. If the assessment shows a generally loose lens diaphragm then the capsulorhexis should made about 5 to 7 mm in diameter being about 0.5 to 1.0 mm larger than the IOL optic diameter, again centered on the optical axis. If the zonular strength assessment shows asymmetric weakness the capsulorhexis should still be 5 to 7 mm in diameter being 0.5 to 1.0 mm larger than the IOL optic diameter, but located off-center away from the possible dehiscence. The would allow the IOL optic to be aligned and centered up with the capsulorhexis when the haptics is orientated toward the quadrant of zonular weakness. Larger diameter capsulorhexis are more difficult because the steepness of the capsule wall increases towards the capsule equator, thus its harder to limit the shear forces without stretching the capsule, and the probability increases of a rhexis escape, i.e., an errant tear.

Errant tears are radial rips and extensions of the capsulorhexis towards the equator, moreover if a zonular attachment is encountered the tear is sent directly out to the capsular fornix and possibly through to the posterior of the capsule. Furthermore, posterior capsule tears facilitate the nucleus being “dropped” into the posterior chamber resulting in further complications.

Further problems that may develop in capsulorhexis are related to inability of the surgeon to adequately visualize the capsule due to lack of red reflex, to grasp it with sufficient security, to tear a smooth symmetric circular opening of the appropriate size or technical difficulties related to maintenance of the anterior chamber depth after initial opening, small size of the pupil, or the absence of a red reflex due to the lens opacity. Additional complications arise in older patients with weak zonules and very young children that have very soft and elastic capsules, which are very difficult to mechanically rupture.

Errant tears and other problems can be managed to some degree with the addition of dense viscoelastics and relaxing incisions to assist in stabilization of the capsule rim. If need be a two-stage capsulorhexis technique can be required to rescue a situation or for the formation of a second large capsulorhexis. Specifically, after creating an initial capsulorhexis, the anterior cortex is removed with aspiration and irrigation and capsule is refilled with viscoelastic to stabilize the capsule and the capsulorhexis is enlarged by tearing larger second capsulorhexis.

Further stress is applied to the capsulorhexis in phacoemulsification and implantation of the IOL, if the capsulorhexis is discontinuous or if the force is too great the capsulorhexis may cause a radial tear. This is dealt with as above. Furthermore if the posterior capsule integrity is damaged during the cataract surgery (i.e., a posterior capsule rent) dense viscoelastic is added to preserve its shape and a posterior capsulorhexis is performed, to salvage the integrity and strength of the capsule around its equator such that an IOL can be implanted.

Most current cataract surgeries are performed with the aid of phacoemulsification and typically includes the following eighteen steps.

-   -   1. Pupil Dilation     -   2. Local Anesthesia     -   3. Placement of the lid speculum     -   4. Entry into the eye through a small incision (typically 2-3 mm         in length, at the edge of the cornea)     -   5. Viscoelastic injected into the anterior chamber and to         maintain the volume and shape of the Anterior chamber and cornea         during the rest of the procedure     -   6. Zonule function test     -   7. Capsulorhexis     -   8. Hydrodissection are intended to identify and soften the         nucleus for the purposes of removal from the eye.     -   9. Hydro-delineation increases the distance between the nucleus         and the posterior capsule, thus providing a safety zone.     -   10. Nuclear cracking or chopping if needed     -   11. Ultrasonic with aspiration and irrigation are used to sculpt         and emulsification of the nucleus used to sculpt the relatively         hard nucleus of the lens.     -   12. Aspiration of the residual soft cortex     -   13. Capsular polishing     -   14. once the capsule is empty further addition of viscoelastic         to maintain the volume and shape of the capsule     -   15. Implantation of the artificial IOL     -   16. Centration of the IOL     -   17. Viscoelastic removal     -   18. Wound sealing/hydration (if needed)

Following cataract surgery there is a rapid 1-2 days response where the capsule hardens and the capsule contraction starts. This continues over a 4-6 week period where fibrosis of the capsulorhexis and IOL optic interface, and the haptic and capsule interfaces also occur. Even beyond one year the capsule continues to contract to a lesser degree, thus positioning the capsulorhexis is a critical factor in the long-term success.

Following cataract surgery one of the principal sources of visual morbidity is the slow development of opacities in the posterior lens capsule, which is generally left intact during cataract surgery as a method of support for the lens, and also as a means of preventing subluxation posteriorly into the vitreous cavity. It has been estimated that the complication of posterior lens capsule opacification occurs within 5 years of surgery with a 10% incidence. This problem is thought to occur as a result of epithelial and fibrous metaplasia along the posterior lens capsule centrally from small islands of residual epithelial cells left in place near the capsule equator. The Q-switch Nd:YAG lasers are utilized as to perform a noninvasive posterior capsulatomy to remove the opacification from the proximity of the optical axis.

Accordingly, there is a need in the art to provide new ophthalmic methods, techniques and apparatus to advance the standard of care for capsulorhexis

SUMMARY OF THE INVENTION

The present invention provides a laser-assisted method for separating tissue such as collagen-containing tissue. In one embodiment, the method is a capsolurorhexis whereby the laser-assisted method is applied to the lens capsule.

A light-absorbing agent is added into or onto the tissue. A light beam with a wavelength capable of being absorbed by the light absorbing agent is then directed at the tissue to cause a thermal effect at the tissue. The light beam is: (i) characterized to remain at a sub-ablation level of the tissue or (ii) characterized to cause melting of the tissue. The light beam could either cause a full or partial separation, cutting or puncture of the tissue.

A predetermined closed curve is defined at the tissue. This curve defines an interior and an exterior. The light beam is directed at an initial and interior point of the predetermined closed curve. Once an initial puncture or partial/full separation has been achieved, the light beam continues and is further directed starting from the initial and interior point of the predetermined closed curve along the remaining path of the predetermined closed curve until at least the curve is closed. In one embodiment, the continued light beam ends at a final and interior point of the predetermined closed curve.

The initial and the continuing light beam(s) could be the same type of light beam or different types of light beams. In a preferred embodiment, the light beam is a laser beam from a CW laser. A CW laser is preferred for at least the continuing light beam to allow for a single pass along the curve to avoid irregularity or potential tears in the resulting rim of the tissue. The exterior path of the predetermined closed curve is preferably substantially circular or ellipsoidal in the application of a capsulorhexis but is not limited to these shapes in other applications.

Visualization patterns could be added and projected at the tissue which will aid in the procedure. The visualization patterns useful in this invention (i) are different from the predetermined closed curve or (ii) include of at least 3 set of dots, wherein each of the set of dots is distributed along the interior-exterior border of the predetermined closed curve.

BRIEF DESCRIPTION OF THE DRAWINGS

The present invention together with its objectives and advantages will be understood by reading the following description in conjunction with the drawings, in which:

FIG. 1 shows according to an embodiment of the present invention a transverse plane view of some parts of the eye (lens capsule 110, IOL 120, dilated iris 140, cornea 160 and anterior chamber 170), a light absorbing agent 130 and a light beam 150.

FIG. 2 shows according to an embodiment of the present invention a side view of the lens capsule 110 whereby the tissue (in this example lens capsule 110) has been separated at 210 into two parts, e.g. an exterior part 110-E and an interior part 110-I. FIG. 2 also shows the contracted and shrinked ends 220-E and 220-I.

FIG. 3 shows according to an embodiment of the present invention a coronal plane view from an anterior direction of a tissue (in this example lens capsule 110) with a predetermined closed curve 310. It is important to note that the predetermined closed curve starts with an initial point inside of the closed curve. In one embodiment, the predetermined closed curve ends at any point where the curve becomes closed. In another embodiment, the predetermined curve end with end-point within the interior area.

FIGS. 4A-B show according to an embodiment of the present invention a visualization pattern 410, which preferably coincides with the perimeter of the closed curve (e.g. a circular pattern in this particular example). It is important to note that the visualization pattern 410 does not include the initial and end paths inside the interior area. FIGS. 4A-B also show another visualization pattern with at least 3 set of dots 420 to assist in focusing the light beam(s), whereby the set of dots preferably are visualized along the interior-exterior border of the closed curve 310. FIG. 4A shows 4 sets of dots and FIG. 4B shows 3 sets of dots. Visualization pattern 410 and 420 could be used separately or together.

DETAILED DESCRIPTION

FIG. 1 shows a transverse plane view of part of the eye. For the purposes of this invention the lens capsule 110 and the IOL 120 are shown including the iris 140 in dilated position. The anterior lens capsule is transparent and therefore does not readily absorb light. Prior attempts to use a laser to remove tissue or make a capsulorhexis in the lens capsule have utilized (i) photodisruption producing cavitation and/or mechanical shockwave, e.g. the Q-switch Nd:YAG lasers used for posterior capsulotomy, or (ii) plasma induced ablation e.g., the sub-pico second laser for 3-D scanned Capsulorhexis and nucleus fragmentation.

In this invention, a light absorbing agent 130 is added into or onto a layer of the anterior lens capsule 110. This agent could be a biocompatible agent (e.g. indocyanine green (ICG) or methyl blue), a dye, pigment, a nanoparticle, a carbon particle, or a like. Subsequently, a light beam 150, e.g. a laser, is directed to the anterior lens capsule. The directed light beam is absorbed by the light absorbing agent with the intent to cause a local thermal affect on the anterior lens capsule that yields a capsulorhexis. In other words, the wavelength, power, speed of light beam movement etc. of the light beam(s), should be selected so that it can be absorbed by the light absorbing agent to cause sufficient thermal energy adjacent or at the anterior lens capsule. Furthermore, the absorption of energy should be sufficient to cause a mechanical separation 210 effect at the anterior lens capsule FIG. 2). In general, the light beam(s) are set to be at a sub-ablation level of the anterior lens capsule or are set to cause local melting or partial/full separation of the anterior lens capsule.

The lens capsule membrane contains collagen fibrils. As collagen is heated, it denatures, i.e. the triple-helix of collagen unwinds due to the disruption of hydrogen bonds between the adjacent alpha chains. Furthermore, collagen undergoes a transition from its crystalline helical structure to an amorphous structure and collagen shrinkage/contraction occurs (220-E, 220-I in FIG. 2). With the application of controlled heat by the directed light beam to the anterior lens capsule in the temperature range between 50 degrees Celsius and 150 degrees Celsius vaporization, membrane melting and shrinkage can occur. In another embodiment, the temperature range could be between 100 degrees Celsius and 120 degrees Celsius.

The capsulorhexis will be formed and the immediately adjacent tissue that forms the resultant rim will have the contracted amorphous collagen. This resulting rim is more elastic and resistant to tearing than the original membrane because it comprises of this amorphous collagen and no additional mechanical forces have stress/fractured the rim during this process. The shrinked and contracted ends 220E and 220-I separate (see 210) as a result of the directed light the anterior lens capsule 110 into the part that remains in the eye 110-E and the part that eventually is removed 110-I for the purposes of a capsulorhexis.

One of the key aspect of the invention is the pattern of the light beam directed at the anterior lens capsule FIG. 3). FIG. 3 is a coronal plane view from an anterior direction of the lens capsule 110. A predetermined closed curve 310 is defined that will be used to direct the light beam(s) and perform the capsulorhexis. The closed curve 310 defines an interior and exterior area, whereby the interior area is enclosed by the closed curved 310 as shown in FIG. 3. The exterior area is anything outside the circumference of the closed curve 310. The predetermined closed curve distinguished an initial starting point (initial) located in the interior area. Optionally the predetermined closed curve also include an ending point (end) located in the interior area. The predetermined closed curve can be (pre)-programmed and added to the laser and optical system used for the performance of the capsulorhexis.

During execution, a light beam is directed to the initial point on the closed curve 310. The selection of the position of the initial point is to create an initial starting hole, puncture or separation in the anterior lens capsule while staying clear from the ultimate position of the rim of curve 310 upon capsulotomy. Since the initial point is inside the closed curve it avoids irregularity or potential tears in the resulting rim of the remaining anterior lens capsule (i.e. 220-E).

Once the initial point is created by the light beam and according to one embodiment, the light beam is directed from the initial point of the predetermined closed curve and continues (in the direction of the error and in this example counterclockwise) along the pattern of the predetermined closed curve until at least the curve is closed. In one embodiment, this endpoint could be at end as shown in FIG. 3 i.e. at the interior part of the closed curve again to avoid irregularity or potential tears in the resulting rim of the remaining anterior lens capsule or in another embodiment at any point once the curve is closed at the border of the interior/exterior area. For the purposes of a capsulorhexis, the shape of the exterior perimeter of the closed curve is preferably substantially circular or ellipsoidal.

The light beam at the initial point or the continued light beam along the curve path could be the same light beam or could be different light beams either with the same of different characteristics or parameters. The initial point could also be seen as an initial puncture before following the path of the curve and, according to this example, the initial light beam could then be different from the continuing light beam.

In one embodiment, for example, but not limiting to the scope of the invention, the initial light beam or puncture could have the following parameters:

-   -   Speed of movement: 0 to 10 mm/second, basically dwelling on one         location or oscillating a small region for a time of about 0.25         to 3 sec.     -   Diameter of light beam on the surface: 50-600 microns.     -   Power of light beam dependent on the light absorbing agent, but         ideally less than 1000 mW.

In one embodiment, for example, but not limiting to the scope of the invention, the continuing light beam which at least closes the curve could have the following parameters:

-   -   Speed of movement: 0.25 to 10 mm/second, preferably in a single         pass along the curve.     -   Diameter of light beam on the surface: 50-600 microns.     -   Power of light beam dependent on the light absorbing agent, but         ideally less than 1000 mW.

In a preferred embodiment, for example, but not limiting to the scope of the invention, the continuing light beam which at least closes the curve could have the following parameters:

-   -   Speed of movement: 0.5 to 3 mm/second, preferably in a single         pass along the curve.     -   Diameter of light beam on the surface: 100-300 microns.     -   Power of light beam dependent on the light absorbing agent, but         ideally less than 600 mW.

The continuing light beam is preferably accomplished in a single pass to provide as much consistency in the rim pattern as possible with the rim being formed with the same (or at least similar) thermal conditions. The single pass is also important to ensure completion of the capsulorhexis even if there is slight movement of the eye relative to the trajectory. Preferably and in particular for the continuing light beam a CW laser is used. However, a high-frequency pulsed (>1 KHz) pulsed laser, e.g. a subpico Q-switch laser could also be used. In one embodiment, the wavelength could be in the infrared to near infrared region of the spectrum, thus it would be near invisible to the patient, providing minimal irritation.

A visible aim beam or pattern(s) could be present to project the laser-cutting or laser-separating trajectory or to project at least part of the closed curve on the anterior lens capsule surface. The visualization patterns are useful to bring the laser into focus on the lens capsule surface and to allow the physician to select the location and size of the capsulorhexis. To get the visible aim beam into focus is often hard, especially for a ring, since you are looking for a sharp edge on the aim beam or its smallest width of the line.

To assist focusing the method described herein could be extended by projecting a visualization pattern 410, which preferably coincides with the perimeter of the closed curve (e.g. a circular pattern in this particular example) (FIG. 4). In other words, a key aspect of this invention is that visualization pattern 410 is different from the pattern of the closed curve 310 (i.e. 410 does not include the initial and end paths in the interior side of the closed curve). FIG. 4 also show another visualization pattern with at least 3 set of dots 420 to assist in focusing the light beam(s), whereby the set of dots preferably are visualized along the interior-exterior border of the closed curve 310. Such a pattern of discrete dots 420 is far easier to focus and or orientating the eye of the patient. Pattern 410 and 420 could be used separately or combined.

In one embodiment, for example, but not limiting to the scope of the invention, the visualization light beam could have the following parameters:

-   -   Speed of movement: greater than 450 mm/second.     -   Diameter of light beam on the surface: 50-600 microns     -   Power of light beam is dependent on the light absorbing agent,         with an average power of less 1 mW.     -   Wavelength is in the visible spectrum.

As one of ordinary skill in the art will appreciate, various changes, substitutions, and alterations could be made or otherwise implemented without departing from the principles of the present invention. For example, in one variation the methods described herein could be varied from the application of a capsolurorhexis to thermally cutting or partially/fully separating tissue or collagen-containing material. In yet another variation, the laser-assisted capsulorhexis does not penetrate the full thickness of the anterior lens capsule, but there is a groove in the capsule surface. The full thickness capsulorhexis could then be completed manually with a CCC with the groove guiding the manual tear. In still another variation, additional methods for fixating the eye could be added for example by placing a surgical contact lens on the eye. This will minimize the eye motion. Moreover, the scanning device could or any other device could hold the contact lens thus restricting the eye motion further. The use of a contact lens could also increase the ability to focus the light with a great numerical aperture, allowing more accurate focusing on the specific target tissue and reduction or eliminate potential light beam exposure to the retina, cornea, fovea posterior capsule and cataractus lens and therewith less of a disturbance/irritation to the patient. Accordingly, the scope of the invention should be determined by the following claims and their legal equivalents. 

What is claimed is:
 1. A device for thermally separating collagen containing tissue, comprising: a laser device having a programmed light beam profile for a predetermined closed curve to be directed at a tissue, wherein said tissue contains: (i) collagen and (ii) a light-absorbing agent, wherein said predetermined closed curve defines an interior and an exterior area, wherein said programmed light beam profile is selected with the intent that said programmed light beam profile is absorbed by said light-absorbed agent to cause a local thermal effect at said tissue and therewith said light beam profile is characterized to: (j) remain at a sub-ablation level for said tissue, and (jj) transition the collagen in said tissue from a crystalline helixcal structure to an amorphous structure resulting in shrinkage or contraction of said tissue, wherein said programmed light beam profile is programmed to be directed at an initial and interior point of said predetermined closed curve, and further programmed to be continued and directed starting from said initial and interior point of said predetermined closed curve along a remaining path of said predetermined closed curve until at least the curve is closed, wherein said tissue is to be thermally separated as a result of said programmed light beam profile executed by said laser device.
 2. The device as set forth in claim 1, wherein said continued light beam is defined to end at a final and interior point of said predetermined closed curve.
 3. The device as set forth in claim 1, wherein said continuing light beam is defined as a continuous light beam to be continued in a single pass.
 4. The device as set forth in claim 1, wherein said programmed light beam profile is defined as a continuous wave during the duration of said direction of said continuing light beam.
 5. The device as set forth in claim 1, wherein an exterior path of said predetermined closed curve is defined as substantially circular or ellipsoidal.
 6. The device as set forth in claim 1, wherein said programmed light beam profile has a laser scanning speed less than 10 mm/s, a light beam diameter of 50 to 600 microns, and a light beam power of less than 1000 mW.
 7. The device as set forth in claim 1, wherein said programmed light beam profile has a laser scanning speed between 0.5 and 3 mm/s, a light beam diameter of 100 to 300 microns, and a light beam power of less than 600 mW.
 8. The device as set forth in claim 1, wherein said programmed light beam profile causes a temperature increase at said tissue in a range between 50 and 150 degrees Celsius.
 9. The device as set forth in claim 1, wherein said programmed light beam profile causes a temperature increase at said tissue in a range between 100 and 120 degrees Celsius.
 10. The device as set forth in claim 1, further comprising said laser device having defined a visualization pattern for projecting said visualization pattern onto said tissue to focus said programmed light beam profile at said tissue, wherein the visualization pattern (i) is different from said predetermined closed curve or (ii) comprises of at least 3 set of dots, wherein each of said set of dots is distributed along an interior-exterior border of said predetermined closed curve.
 11. The device as set forth in claim 1, wherein said visualization pattern has a visualization beam with a speed greater than 450 mm/s. 